Systems and methods for fluid flows and/or pressures for circulation and perfusion enhancement

ABSTRACT

Fluid pressure or flow in a human body may be adjusted with circulation or perfusion systems and methods. The system may include a first pump implantable in a chamber or vessel of the human body, and a plurality of struts connected to a housing of the first pump, wherein the struts secure the first pump in a desired location of the chamber or vessel. The system may also include one or more flow modification elements disposed on the first pump, where the flow modification elements direct flow to a desired organ or a desired vessel to adjust pressure or flow as desired.

RELATED APPLICATIONS

This application is a divisional of U.S. Pat. No. 9,572,915 filed onMar. 26, 2013, which claims the benefit and priority of U.S. ProvisionalPatent Application No. 61/615,716 filed Mar. 26, 2012, which areincorporated herein by reference.

FIELD OF THE INVENTION

This invention relates to a circulatory support system and method. Moreparticularly, to systems and methods for vessel or end organ perfusion.

BACKGROUND OF INVENTION

Circulation and Perfusion Enhancement

Circulation of blood throughout the body and perfusion of end organs arebasic functions in humans and most other animals. Many differentproblems and conditions result when this circulation is altered,obstructed, interfered with, or changed. Substantially all of the bodyis dependent on circulation for delivery of oxygen and nutrients andremoval of waste products. If the pressure or flow rate of circulationto a certain organ or region of the body changes, that certain organ orregion can experience loss of function, tissue death, or otherimpairment.

Some of the organs most dependent on optimal circulation are those thatprocess the blood for the benefit of the entire body. For example, thekidneys, liver and spleen remove waste products or unneeded materialfrom the blood. The small intestine transfers nutrients from consumedfood to the blood. Changes to the circulation (also called perfusion) ofthese organs can have ill effects on the entire body.

Parts of the body that do not process blood for the benefit of the bodyalso suffer from poor circulation. Peripheral vascular disease ischaracterized by poor circulation to the extremities. Symptoms includeswelling, numbness, loss of function, pain, and tissue death. In seriouscases, the affected limb or extremity can become gangrenous andamputation is required.

Methods for addressing poor circulation or perfusion include medicationsthat increase the contractility of the heart (inotropes), reduce thefluid load on the heart to improve its function (diuretics), or openblood vessels to increase flow (vasodilators). These medications havedisadvantages including, but not limited to, deleterious side-effects,habituation, partial effectiveness, or ineffectiveness. For example,inotropes can increase the risk of death. Diuretics and vasodilatorsinterfere with some of the body's natural compensatory mechanisms,indicating their use involves some trade-off. For example, diuretics mayreduce fluid load without actually addressing the underlying poorcirculation that led to increased fluid load and vasodilators mayincrease flow but at reduced pressure (adequate perfusion requiresadequate flow and pressure).

Mechanical devices are also used to improve circulation. Two classes ofsuch devices are left ventricular assist devices (LVADs) andintra-aortic balloon pumps (IABPs). LVADs are pumps that are surgicallyimplanted in the chest cavity and connected between the left ventricleof the heart and the aorta to augment the heart's output. IABPs arecatheter based devices with a large balloon that inflates inside theaorta while the aortic valve is closed (i.e. during diastole) to forceblood further into the circulatory system.

These mechanical devices have disadvantages also. LVAD implantationrequires major open heart surgery in a well-equipped operating room andhas a lengthy recovery period (forty days or more). Total cost for theprocedure can range from a few hundred thousand to a million dollars ormore. Additionally, serious complications (e.g. stroke or infection)from the procedure are common. IABPs are safer, but usually limited toshort-term in-hospital use. In addition, the effectiveness of an IABP isdirectly related to the size of the balloon and larger balloons canextend past branches off the aorta (e.g. the phrenic, superiormesenteric, celiac, and renal arteries) that supply blood to several keyorgans. In this case, these organs may see only limited improvement (oreven reduction) in circulation.

In addition to the disadvantages described above, medications, VADs, andIABPs provide systemic level circulatory support that is difficult orimpossible to adjust in magnitude or limit to or localize in or focus ona particular organ, area, region, or part of the body. Drug therapytakes some time to have significant impact and is not practical foremergency or acute or short term improvement to circulation orperfusion. LVADs are also not practical for emergency or acute or shortterm improvement to circulation or perfusion due to the expense,invasiveness, planning, and time required for LVAD implantation.

One helpful context in which to judge, without limiting, the advantageof a system for creating specific enhancements to circulation andperfusion over blood pumps delivering non-specific systemic support isin the treatment of shock.

When a person's tissues are starved of oxygen rich blood over time, theperson may enter a state of shock. Shock, usually caused by sepsis,hemorrhage, or acute heart failure, causes millions of deaths per year.Over half of shock patients die, usually as a result of multiple organfailure (MOF). The kidneys are at the root of multiple organ failure:poor perfusion of the renal arteries begins a dangerous feedback loopthat can lead to damage of numerous organ systems.

For this reason, prevention of end organ failure is most often focusedon supporting the kidneys. Traditional treatments include pharmacologictherapies, IV fluid optimization, vasopressors, and eventually renalreplacement therapy (e.g. dialysis). Current therapeutic guidelines havenot changed in decades, despite the fact that no pharmacologic treatmenthas been proven effective in clinical trials and excessive IV fluidburden can cause peripheral and pulmonary edema. Furthermore, the use ofpressors to increase blood flow to the kidneys can cause acute andpermanent ischemic damage to extremities and other organs.

Mechanical cardiovascular or circulatory support (MCS) to increase bloodflow and pressure to the kidneys and/or other end organs is a novelapproach to the treatment of shock. Current MCS treatment devices ormethods are generally targeted at supporting the coronary vasculatureduring acute periods of cardiogenic shock, such as following amyocardial infarction or during percutaneous coronary intervention.Among these current approaches, a device that can be configured, withoutlimitation, to deliver specific enhancements in circulation andperfusion, e.g., to improve renal clearance, would be an indispensabletool for cardiovascular or circulatory support.

The systems and methods discussed herein provide cardiovascular support,configurable flow and pressure management, and selective perfusion ofspecific targeted vessel(s) and end organ(s). Non-limiting examples ofuses may include increasing renal perfusion to treat acute/chronickidney injury; treating cardiogenic, septic, hypovolemic, or hemorrhagicshock; changing carotid perfusion to avoid ischemic stroke or balancethe effect of downstream pumps; changing celiac/mesenteric perfusion totreat obesity or bowel ischemia; increasing liver perfusion to treatliver disease; improving perfusion of the heart itself by pulling bloodfrom the coronary sinus, pushing blood into the coronary sinus, orpushing blood into the coronary arteries; and/or diverting flow awayfrom sources of bleeding.

SUMMARY OF INVENTION

In one embodiment, a system for adjusting pressure of flow in a humanbody may include a first pump implantable in a chamber or vessel of thehuman body, and a plurality of struts connected to a housing of saidfirst pump, wherein said struts secure the first pump in a desiredlocation of said chamber or vessel. The system may also include one ormore flow modification elements disposed on said first pump, where saidflow modification elements direct flow to a desired organ or a desiredvessel to adjust pressure or flow as desired. In some embodiments, thesystem may provide one or more additional pumps. The position ororientation of the pumps and flow modification elements may be orientedto assist native flow, increase or decrease pressure in a region, directflow in a direction opposite of native flow, direct flow towards desiredvessel(s) or organ(s), or a combination thereof.

In another embodiment, a method for adjusting fluid flow or pressurewithin a human body is provided. The method may include transluminallyinserting a pumping system in a desired chamber or vessel the humanbody. The pumping system a pump, a plurality of struts, and one or moreflow modification elements. The method may also include deploying saidplurality of struts to secure said pumping system in the desired chamberor vessel. In some embodiments, the pumping system may provide one ormore additional pumps. The position or orientation of the pumps and flowmodification elements may be oriented to assist native flow, increase ordecrease pressure in a region, direct flow in a direction opposite ofnative flow, direct flow towards desired vessel(s) or organ(s), or acombination thereof.

The foregoing has outlined rather broadly various features of thepresent disclosure in order that the detailed description that followsmay be better understood. Additional features and advantages of thedisclosure will be described hereinafter.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present disclosure, and theadvantages thereof, reference is now made to the following descriptionsto be taken in conjunction with the accompanying drawings describingspecific embodiments of the disclosure, wherein:

FIG. 1A is a partial cross-sectional view of a heart, to illustrate itsfunctions and anatomy;

FIG. 1B is a partial cross-sectional view of the intravascular pumpingmodule of the present invention in a first transluminal deliveryconfiguration, the device being enlarged for clarity];

FIG. 1C is a partial cross-sectional view of intravascular pumpingmodule in accordance with the present invention in a second deployedconfiguration;

FIG. 1D is a partial cross-sectional view of another embodiment of theintravascular pumping module in accordance with the present invention ina second deployed configuration;

FIG. 1E is a partial cross-sectional view of an embodiment of theintravascular pumping module in accordance with the present inventionincluding a one-way valve;

FIG. 1F is a partial cross-sectional view of another embodiment of theintravascular pumping module of the present invention in a firsttransluminal delivery configuration, the device being enlarged forclarity;

FIG. 1G is a partial cross-sectional view of another embodiment of theintravascular pumping module in accordance with the present invention ina second deployed configuration;

FIG. 2A shows a pump configuration;

FIG. 2B shows an inline pump configuration;

FIG. 3 is an illustrative embodiment of an entrainment method using asource/reservoir separated from upstream flow of a pump;

FIG. 4 is an illustrative embodiment of auto-entrainment;

FIG. 5 is an illustrative embodiment of reverse bypass flow;

FIGS. 6a and 6b are illustrative embodiments of position, orientation,and configuration of an intravascular pumping module in a vessel;

FIG. 7 is an illustrative embodiment of an intravascular pumping moduleconfigured to minimize reverse bypass flow;

FIGS. 8a and 8b are illustrative embodiments of a series flowaugmentation (a) and a parallel flow augmentation (b);

FIG. 9 is an illustrative embodiment of an intravascular pumping module;

FIG. 10 is another illustrative embodiment of an intravascular pumpingmodule;

FIG. 11 is yet another illustrative embodiment of an intravascularpumping module;

FIGS. 12A-1 to 12D-1 and 12A-2 to 12D-2 are illustrative embodiments ofaxiosymmetric (a), axis-parallel (b), axis-intersecting (c), and skeworientations of devices in a vessel (d);

FIG. 13 is an illustrative embodiment of devices with a flexiblecannula;

FIGS. 14a-14c are illustrative embodiments of flat (a), conical (b), andellipsoid shaped (c) nose cones;

FIG. 15 is an illustrative embodiment of inlet flow;

FIGS. 16a-16d are illustrative embodiments of a flat nose cone withaxial ports (a), a flat nose cone with radial ports (b), an ellipsoidnose cone with axial ports (c), and an ellipsoid nose cone with radialports (d);

FIG. 17 is an illustrative embodiment of a non-symmetric, hybrid inlet;

FIGS. 18a-18d are illustrative embodiments of axial inlet ports (b) andradial inlet ports (a, c) and non-symmetric inlet ports (d);

FIGS. 19a-19c are illustrative embodiments of flat (a), conical (b), andellipsoid shaped (c) tail cones;

FIG. 20 is an illustrative embodiment of outlet flow;

FIGS. 21a-21d are illustrative embodiments of a flat tail cone withaxial ports (a), a flat tail cone with radial ports (b), an ellipsoidtail cone with axial ports (c), and an ellipsoid tail cone with radialports (d);

FIG. 22 is an illustrative embodiment of a non-symmetric, hybrid outlet;

FIGS. 23a-23d are illustrative embodiments of axial outlet ports (b) andradial outlet ports (a, c) and non-symmetric outlet ports (d);

FIGS. 24a-24i are illustrative embodiments of various outlet portnozzles;

FIGS. 25a-25g are illustrative embodiments of various flow directors;

FIGS. 26a-26d are illustrative embodiments of devices utilizing multiplemotors, pumps, and/or cannulas;

FIG. 27A is an illustrative embodiment of intravascular pumping modulewith struts deployed;

FIG. 27B is an illustrative embodiment of intravascular pumping modulein a sheath;

FIG. 28A is an illustrative embodiment of intravascular pumping moduleimplanted in a vessel;

FIG. 28B is an enlarged view of intravascular pumping module implantedin a vessel;

FIG. 28C shows the intravascular pumping module implanted in thedescending thoracic aorta superior to splanchic arteries;

FIG. 29A shows left ventricular contractility;

FIG. 29B shows end-systolic pressure-volume relationship (ESPVR) beforeheart failure and with the intravascular pumping module on or off;

FIG. 29C shows left ventricular pressure over time when intravascularpumping module is on or off;

FIG. 29D shows left ventricular volume over time when intravascularpumping module is on or off;

FIG. 30 shows the percentage change in Ea, SW, EDP, CO, SV, and EF %;

FIG. 31A shows renal flow and pressure when intravascular pumping moduleis on or off;

FIG. 31B shows renal flow and pressure over time;

FIG. 32 shows two pumps working together to produce a limited region ofhigh pressure;

FIG. 33 shows configuration of outlet ports to selectively enhancekidney perfusion;

FIG. 34A shows a device placed upstream of the renal arteries;

FIG. 34B shows a device placed at the iliac bifurcation;

FIG. 34C shows a device placed in a renal artery;

FIG. 34D shows a device placed in an inferior vena cava;

FIG. 35 shows a two-pump embodiment for renal perfusion;

FIG. 36 shows a computer simulation of auto-entrainment in a flow loop;

FIG. 37 shows results of a computer simulation of auto-entrainment; and

FIG. 38 shows results of bench top experiments on auto-entrainment.

DETAILED DESCRIPTION

Refer now to the drawings wherein depicted elements are not necessarilyshown to scale and wherein like or similar elements are designated bythe same reference numeral through the several views.

Referring to the drawings in general, it will be understood that theillustrations are for the purpose of describing particularimplementations of the disclosure and are not intended to be limitingthereto. While most of the terms used herein will be recognizable tothose of ordinary skill in the art, it should be understood that whennot explicitly defined, terms should be interpreted as adopting ameaning presently accepted by those of ordinary skill in the art.

It is to be understood that both the foregoing general description andthe following detailed description are exemplary and explanatory only,and are not restrictive of the invention, as claimed. In thisapplication, the use of the singular includes the plural, the word “a”or “an” means “at least one”, and the use of “or” means “and/or”, unlessspecifically stated otherwise. Furthermore, the use of the term“including”, as well as other forms, such as “includes” and “included”,is not limiting. Also, terms such as “element” or “component” encompassboth elements or components comprising one unit and elements orcomponents that comprise more than one unit unless specifically statedotherwise.

Systems and methods for series modification of flow and/or pressure tocreate circulation of perfusion enhancements targeted to specificvessels and/or end organs are discussed herein. The systems and methodsallow for managing the flow and/or pressure of fluids to create specificcirculation or perfusion enhancements in one or more vessels or chambersof the human body by utilizing one or more pumps implanted withinchambers or vessels of the human body. This is series flow augmentation,accomplished within the vasculature and without creating alternative orparallel flow paths.

This application describes systems and methods for using intravascularblood pumps, together with novel flow and pressure modificationelements, to selectively augment, control and/or adjust the perfusion oftargeted branch vessel(s) and/or end organ(s) in specific ways. Anexemplary embodiment of such an intravascular blood pump is described inU.S. Pat. No. 8,012,079, which is incorporated by reference herein. Anonlimiting embodiment of a circulation and perfusion enhancement systemmay comprise such an intravascular blood pump fitted with flow andpressure modification elements and secured to the wall of a vessel orlumen or chamber with a securing means. In a nonlimiting embodiment, thecirculation and perfusion enhancement system is disposed along thecentral axis of the vessel or lumen or chamber without significantlyblocking the path of native blood flow. The securing means may extendfrom the pump and/or flow and pressure modification elements to securethe pump and flow and pressure modification elements to the wall of avessel or lumen. This securing means also does not significantlyobstruct native blood flow as it passes around the circulation andperfusion enhancement system.

The circulation and perfusion enhancements created by the circulationand perfusion enhancement system can be well specified along a number ofdimensions. Without limitation, the circulation and perfusionenhancements the circulation and perfusion enhancement system may createinclude increased or decreased fluid flows of various velocities and invarious directions, flows that are turbulent or laminar, flows that mixquickly or slowly with native blood flow, flows that are targeted forspecific end organs, regions of increased or decreased pressure that maybe diffuse or tightly focused, or a combination thereof.

In addition to the ability to achieve specific and defined enhancementsto circulation and perfusion, the circulation and perfusion enhancementsystem design and size allow freedom of placement in many vessels orchambers of the body. These characteristics give the circulation andperfusion enhancement system distinct advantages over other mechanicalcirculatory support options.

Active and Ambulatory Patient Recovery: Surgically implanted VADs areone potential option for patients with cardiogenic shock unresponsive toinotropic therapy. However, their use has been limited by the risksassociated with implantation and the cost of current devices. VADsrequire a long, technically complex, open heart surgery with added riskof death, injury, and infection. Furthermore, only a small number ofspecialized medical centers with experienced surgeons can properlyimplant these pumps. At the other end of the spectrum, percutaneousmechanical cardiovascular or circulatory support (MCS) devices are lessinvasive, but do not allow for patient ambulation and are not fullyimplantable.

In some embodiments, the systems and methods discussed herein may allowa pump to be deployed through a catheter percutaneously or by minorsurgical access to the vasculature. In some embodiments, the systems andmethods provide a fully implantable cardiac assist device due to theability to use an implantable battery and transcutaneous charging. Sincethere will be no indwelling leads or open surgery, the patient will havethe ability to ambulate early in recovery, which has been shown tosignificantly decrease recovery time and length of stay. In someembodiments, the system may be anchored by struts in its safe location(i.e. downstream of the carotids and away from organs and valves) in thedescending aorta or other vessel locations to provide stability thatallows for patient mobility and ambulation. In contrast, IABPs haveunanchored positioning and intracardiac percutaneous VADs are positionedacross the aortic valve. Devices with a pneumatic or mechanicaldriveline have a risk of vessel injury or kinking or loading the linewith patient movement. The systems and methods discussed herein providea fully implantable design that reduces or avoids these risks and allowsfor faster patient recovery.

Safety: In some embodiments, the system is deployed in a specificlocation in the descending aorta or one of its branch vessels (e.g. theceliac, superior mesenteric, renal, inferior mesenteric, gonadal, iliac,or subclavian) away from the heart or end organs and downstream of thecarotid arteries. For example, in a nonlimiting embodiment, the pump maybe inserted from a femoral or iliac site and deployed in the descendingthoracic aorta. Such deployment positions of the systems and methodsdownstream of the carotids discussed herein have drastically reducedrisks compared to other blood pumps that discharge upstream of thecarotids or that are deployed across the aortic valve into the leftventricle and/or upstream of the carotids. Placement upstream of thecarotids drastically reduces the chance of our system causing an embolicstroke or the like. Avoiding placement across the aortic valve is saferfor use in patients with valvular disease and carries a lower risk ofdamaging the native valve. In some embodiments, the system may bedelivered via catheter with a single access site at or near the femoralor iliac or other major artery or vein. Compared to the risky open heartprocedure for traditional VADs or the atrial septum puncture required byother less-invasive VADs, complication rates should be greatly reduced.Further, the system takes up only a fraction of the cross sectional areaof the aorta and allows blood flow around the device, thereby greatlyreducing risks that may arise from pump failure. The system's smallcross sectional area also allows interventionists to performsimultaneous cardiac catheterization procedures via the femoral accesssite by passing catheters around our system while it is in place andfunctioning.

Hemodynamics & Function: In one embodiment, the system is positionedimmediately proximally to the renal and mesenteric arteries andincreases both systolic and diastolic pressure and flow to these vesselswhile preserving the native pulsatile flow waveform (which may producehealthier perfusion than VADs that eliminate pulsatility which sometimessee conditions like acquired von Willebrand syndrome and gastricbleeding), In this embodiment, the system creates a pressure gradientthat causes both cardiac load reduction and a constant increase in bothpressure and flow downstream to key end organs, including the kidneys.IABPs, on the other hand, modify aortic pressure to reduce cardiac loadduring systole, but may actually decreases mean arterial pressure (MAP)to end organs. The system is simpler than IABPs in that noelectrocardiography (ECG) sync is required. This functionality, inaddition to our continuous flow design, makes the system uniquelysuitable for patients with tachyarrhythmia or atrial fibrillation.Traditional, less invasive, and intra-cardiac percutaneous VADs work inparallel with the left ventricle, taking over a large percentage of thecardiac output. These devices increase cardiac load, making it moredifficult for the heart to naturally eject blood through the aorticvalve. Our system functions in series with the heart, meaning the heartstill ejects the total cardiac output naturally across the aortic valve,but with the assistance of our device. This assistance may manifest asincreased cardiac output, increased ejection fraction, reducedafterload, reduced aortic root pressure, the aortic valve openingearlier in the cardiac cycle and remaining open longer during thecardiac cycle, and/or reduced work of the heart. These simply achievedbut significant flow and pressure benefits will also be present innon-aortic placements of our device.

To summarize, some advantages of the circulation and perfusionenhancement system over traditional or less-invasive surgical VADs areease of insertion (no surgeon, operating room, or OR-type sterileconditions required), speed of insertion (minutes not hours),non-invasiveness (low risk, low stress on possibly old or injured body),lower stroke risk (downstream of carotids), greater suitability for TET(which provides lower infection risk), maintained pulsatility,unobstructed native blood flow (which can flow right around the deviceif it partially or completely fails), specificity of circulation orperfusion enhancement, and greater suitability for short term use.

Some advantages of the circulation and perfusion enhancement system overintracardiac percutaneous VADs are no hardware across the aortic valve,no hardware in the heart, higher suitability for long term use, lowerstroke risk, and specificity of circulation or perfusion enhancement.

Some advantages of the circulation and perfusion enhancement system overIABPs are more control over pressure profile (can alter systolic anddiastolic pressures without affecting flows), smaller size (lessocclusion of vertebral and renal and mesenteric and celiac arteries;large size of balloon makes enhanced perfusion of these arteriesdifficult to predict and control), potential for long term use, and noreduction of MAP or flattening native hemodynamics.

The circulation and perfusion enhancement system acts through seriesflow augmentation. This is the case where the entire device lies insidethe vessel or chamber and no alternative or parallel flow path iscreated or used. FIGS. 8a and 8b illustrates the difference between (a)series flow augmentation and (b) parallel flow augmentation. In seriesflow augmentation (FIG. 8a ), the pumped flow (76) physically takes theplace of a portion of the native flow path (74) in some part of thevessel or chamber. In parallel flow augmentation (FIG. 8b ), the pumpedflow (80) is separate and apart from the native flow path (78) and doesnot physically take the place of any part of the native flow path (78).In general, parallel flow augmentation is more complicated, since thealternative flow path must be established. In addition, areas werenative blood flow is artificially split and recombined tend to bethrombogenic.

The circulation and perfusion enhancement system can produce a varietyof hemodynamic effects including, without limitation, large or smallincreases in flow that are laminar or turbulent, guided in a desireddirection, with high or low velocity, and with or without swirl; flowsor pressure gradients opposite the physiological norm; and large orsmall increases or decreases in pressure that are diffuse or tightlyfocused. These effects can be leveraged to produce swirl in the mainvessel or increase or decrease perfusion (which is a function of flowand pressure) through various branch vessels or to specific end-organs.Swirl may stimulate the endothelium to release NO and other compoundsthat improve the arterial tone and reduce SVR. Changes in perfusion may,without limitation, give an ailing kidney more blood flow, promotehealing in an extremity, starve a growing tumor, or rest and heal theheart. The parameters of the circulation and perfusion enhancementsystem that determine the magnitude of the hemodynamic effects include,without limitation, its configuration (number and physical relationshipof pumps and impellers), its location and orientation, its speed andpower, the design of its flow and pressure modification elements, andits pattern of operation. Adjusting these parameters allowsspecification of desired combinations of effects useful for treatingvarious diseases or conditions.

In one embodiment (FIG. 9), a circulation and perfusion enhancementsystem comprises a pump (82) to accelerate fluid flow within a housing(84) with inlet ports (86) and outlet ports (88). This is the “push”configuration. Other embodiments may reverse the flow through the devicedescribed in FIG. 9 such that the ports (88) farther from the pump (82)are inlet ports and the ports (86) closer to the pump (82) are outletports. This is the “pull” configuration.

FIG. 10 shows one embodiment of an intravascular pumping module,comprising a motor (90) driving a shaft (92) connected to an impeller(94). The impeller (94) lies inside the inlet housing (96) which is inturn connected to a flexible cannula (98) which is in turn connected toan outlet housing (100). The inlet housing (96) is connected to themotor (90). The inlet housing comprises an inlet flow director (102) andan intermediate flow director (104). The outlet housing comprises anoutlet flow director or nozzle (106).

FIG. 11 shows another embodiment of an intravascular pumping module,comprising a motor (108) driving a shaft (110) connected to an impeller(112). The impeller (112) lies inside the outlet housing (114) which isin turn connected to a flexible cannula (116) which is in turn connectedto an inlet housing (118). The outlet housing (114) is connected to themotor (108). The inlet housing comprises an inlet flow director (120).The outlet housing comprises an intermediate flow director (122) and anoutlet flow director or nozzle (124). This embodiment has very similarcomponents and a reversed flow direction compared to the embodimentshown in FIG. 10.

As mentioned above, in embodiments with pumps with an impeller attachedto the shaft of a rotary motor, a pump may be in the “push” or “pull”configuration. This is independent of whether the pump is pumping in oragainst the direction of native flow. In the push configuration, themotor is located at the inlet end of the pump, such that fluid enteringthe pump's inlet(s) moves past the motor to do so and fluid exiting thepump's outlet(s) is not obstructed by the motor. In the pullconfiguration, the motor is located at the outlet end of the pump, suchthat fluid entering the pump's inlet(s) is not obstructed by the motorand fluid exiting the pump's outlet(s) moves past the motor to do so.The selection of configuration may be important in various embodiments.For example, if the embodiment includes a cannula on the side of theimpeller opposite the motor, fluid in that cannula will be at negativerelative pressure if the pump is in the pull configuration and atpositive relative pressure if the pump is the push configuration. Fluidslike blood may behave differently (for example, in terms of hemolysis)when exposed to those different pressure environments.

In some embodiments, the circulation and perfusion enhancement system isan intravascular blood pump that, together with the flow controlelements, is delivered transluminally to the implantation site. For thepurposes of illustration and clarity, the circulation and perfusionenhancement system is shown without flow control elements in FIG. 1C.The following nonlimiting example discusses placement of the circulationand perfusion enhancement system in the descending aorta. However, inother embodiments, placement can be in any accessible vessel or chamberof sufficient size. With reference to FIGS. 1B and 1C, in certainembodiments, the intravascular pumping module 80 of the presentinvention may include: a pump 110 which is percutaneously andtransluminally delivered to a portion of the descending aorta 98 orother vessel or chamber (FIGS. 1A and 1C) of a patient 79 via thesubclavian, iliac, or femoral artery 10 (FIG. 1B) of the patient 79; anda transluminally deliverable support structure 120 which secures, oranchors, pump 110 within the descending aorta 98 or other vessel orchamber. Intravascular pumping module 80 may be disposed within aportion of the descending aorta 98 or other vessel or chamber. Incertain embodiments this disposition is preferably in a central portionof the descending aorta 98 or other vessel or chamber. Pump 110 pumpsblood 81″ drawing it downward from the ascending aorta 76, anddischarging it further downward. Thereafter the oxygenated blood 81″from left ventricle 72 is circulated through the various arteries of thepatient's body.

It should be apparent to one of ordinary skill in the art that otherpumps 110, e.g. radial or displacement pumps, could be utilized in lieuof axial flow pump 111, provided pump 110 meets the required dimensions,may be used in a particular embodiment of the device, is bio-compatibleand capable of operating in the environment of the body, specificallythe aorta or other vessel or chamber, and able to pump blood. The pumpor pumps in any particular embodiment may be driven electrically,pneumatically, mechanically or by any other method.

Still with reference to FIGS. 1B and 1C, in this embodiment pump 110 isa rotary pump and preferably is an axial flow pump 111 having first andsecond ends 112, 113, and pump 110 is preferably disposed within ahousing 114. At least one spiral vane, or impeller, 115 is disposedwithin housing 114. Housing 114 may be approximately 18 French diameterin size, although other sizes may be selected. Pump 110 is preferablypowered by a motor 116, such as an electric motor 116′, which rotatesimpeller 115. Impeller 115 may be mounted on a shaft supported bybearings, or magnetically or hydrodynamically levitated, for rotationwithin housing 114. A power wire 117 is associated with motor 116, andas will hereinafter described in greater detail, it extends fromintravascular pumping module 80 to a point at which it may be associatedwith a power source, such as a battery (not shown). Housing 114 may beprovided with a top cover, or inflow cage, 118, which permits thepassage of blood 81″ into housing 114, as it is drawn into, pumped, orpulled into housing 114 by the rotation of impeller 115. Housing 114 ispreferably made of a suitable metallic or plastic material, such asstainless steel, which is a bio-compatible material. Alternatively,other bio-compatible materials, including plastic materials, having therequisite strength and bio-compatibility characteristics which permitthe desired use in a person's aorta or other vessel or chamber may beutilized.

Pump 110 may be powered by an implanted power device, or transformer,and may receive electric power from either an implanted power source orfrom a source of power located outside the patient's body 79. It shouldbe readily apparent to one of ordinary skill that if desired other typesof power could be utilized to power pump 110, such as hydraulic power orother types of power sources. The implanted power device, not shown,could be a conventional battery or a plutonium, or other nuclearmaterial, power source.

In some embodiments, the diameter of the pump 110 will be less than thediameter of the vessel or chamber it is implanted in to provide a bypassregion around the pump and move on without passing through the pump.Alternatively, fluids can recirculate through the pump one or more timesby moving through the bypass region from the outlet of the pump to theinlet of the pump. The bypass region may be provided between pumphousing and a wall surface of a vessel. For example, the embodimentshown in FIG. 1C provides a bypass region between pump housing 114 andwall surface 98′ of aorta 98 or other vessel or chamber. Intravacsularpumping module 80 allows fluids to flow around or past the pump 80through this bypass region. Further, when pump 110 is in operation,fluids may also flow into inlet 112 and out from outlet 113. Pump 110and additional flow or pressure modification elements discussed hereinmay be designed to significantly impact the characteristics of thisbypass flow.

In other embodiments, the diameter of the pump will occupy substantiallythe full diameter of the vessel or chamber the pump is implanted in. Inthese embodiments there will be essentially no bypass flow.

A series flow pump with a bypass region (FIG. 4) has advantages over apartitioned inline pump (FIG. 2B). The lack of partition eithersimplifies configuration (since a partition is not required) or enablesthe pump to be placed in more locations (since no artificial barrier ornatural partition like a heart valve or septum is necessary). The lackof provided partition in locations where no natural partition is presentalso reduces or eliminates the impedance to native flow. In cases wherethe pump fails, for example, the native flow is almost completelyblocked in a partitioned inline pump whereas a failed pump in anauto-entrainment configuration provides a much less obstructed path fornative flow. One advantage of series flow augmentation is the ability toaugment flow in a vessel or chamber with no requirement to place a valveor add additional flow paths or make any changes to the vessel orchamber.

Still with reference to FIGS. 1B and 1C, support structure 120 ofintravascular pumping module 80 includes a plurality of support members121 associated with pump 110, which are may be associated with housing114 or attached to any part of the system. Support members 121 may besecured to the outer surface, or outer wall surface 114′, of housing 114in any suitable manner, such as by welding or adhesive bonding. Thesestruts may be located at any positions. Support structure 120 supportspump 110 within the descending aorta 98 or other vessel or chamber, incertain embodiments, preferably in a generally, centrally spacedrelationship from the interior wall surface 98′ of descending aorta 98or other vessel or chamber. As will be hereinafter described in greaterdetail, support structure 120 anchors pump 110 within descending aorta98 or other vessel or chamber for long or short term use to assist thepumping of blood 81″ from ascending aorta 76 downwardly throughdescending aorta 98 or other vessel or chamber. At least two supportmembers, or struts, 121 are disposed toward the upper end 112 of pump110 and toward the lower end 113 of pump 110. Preferably, at least threesupport members, or struts 121, are substantially equidistantly disposedaround each of the upper and lower ends 112, 113 of pump 110.Preferably, the support members 121 are formed of a suitablebio-compatible material, such as stainless steel or nitinol.Alternatively, other bio-compatible materials, including plasticmaterials, having the requisite strength, expansion or spring, andbio-compatible characteristics to function in the manner hereinafterdescribed in a person's aorta or other vessel or chamber 98 may also beutilized.

Other devices and structures could be utilized for support structure120, provided they permit the percutaneous transluminal delivery of theintravascular pumping module 80, and that after such delivery, thesupport structure 120 permits the disposition of the intravascularpumping module within the descending aorta or other vessel or chamberfor long or short term use, as shown in FIG. 1C. By use of the terms“long term” and “long-term use”, it is meant to be more than therelatively short period of time that conventional percutaneous leftventricular assist devices (LVADS) are used for (e.g. greater than 7-10days, as previously described), and preferably on the order of at leasta month and perhaps even a year or more. For example, a self-expandingstent 200, or stents, as are known in the art could be used forsupportive structure 120, to support pump 110 in a substantiallycentrally spaced relationship from the interior wall surface 98′ ofaorta 98 or other vessel or chamber, as shown in FIGS. 1F and 1G. Thestent, or stents, 200, schematically shown in FIGS. 1F and 1G, couldhave pump 110 centrally disposed therein with support members, or struts121, being attached to the interior of the stent as shown in FIG. 1F.

As shown in FIG. 1B, the support structure 120, or plurality of supportmembers 121 are disposed in a first configuration for percutaneoustransluminal delivery to the desired portion of the descending aorta 98or other vessel or chamber, as will be hereinafter described. In thefirst configuration, support members 121 are disposed substantiallyadjacent the outer wall surface 116 of housing 114, and are disposedsubstantially parallel to the longitudinal axis 119 of housing 114. Inthis first configuration, the overall diameter of pump 110, housing 114,and support structure 120 is reduced to permit the percutaneoustransluminal delivery of the intravascular pumping module 80 through thefemoral or iliac artery 10 of the patient to the desired location withinthe descending aorta 98 or other vessel or chamber or other vessel orchamber.

The support members, or struts 121, may be disposed in thepre-deployment configuration shown in FIG. 1B as by a sheath 130 orannular bands (not shown), which may be subsequently removed, oralternatively, the struts, or support members 121, when initiallyattached to the outer wall surface 114′ of housing 114, have thedisposition shown in FIG. 1B.

In this pre-deployment configuration, the support members, or struts121, may be placed so that the struts fit into depressions or flexibleareas in the motor or housing so as to minimize or eliminate anyincrease over the diameter of the housing. In such an embodiment, thehooks at the end of the struts, which might normally cause the biggestincrease in diameter, could be place so they fit into the device portsin the pre-deployment configuration.

Upon the intravascular pumping module 80 being positioned within thedesired portion of the descending aorta 98 or other vessel or chamber,the support members, or struts, 121, have a second, expandedconfiguration wherein the outer ends 122 of the support members 121contact the inner wall surface 98′ of descending aorta 98 or othervessel or chamber. The second disposition of the support members 121shown in FIG. 1C may be achieved in a variety of ways. For example, thesupport members 121 may be formed as leaf springs, or spring members,wherein the support members 121 are biased to spring outwardly into theconfiguration shown in FIG. 1C. If support members 121 are in the formof leaf springs which bias outwardly toward descending aorta 98 or othervessel or chamber, they may be initially restrained into theconfiguration shown in FIG. 1B, by a sheath 130 or band-like member, aspreviously described, which may be removed when intravascular pumpingmodule 80 has been delivered to its desired location within thedescending aorta 98 or other vessel or chamber, whereby the supportmembers, or struts, 121 would move outwardly into the configurationillustrated in FIG. 1C. Alternatively, support members 121 could beformed of a material, such as nitinol, whereby the support members 121would initially have the configuration shown in FIG. 1B, and upon beingheated by a resistive or inductive heater or by the blood flowing withinaorta 98 or other vessel or chamber would spring outwardly into theconfiguration illustrated in FIG. 1C.

Alternatively, as shown in FIGS. 1F and G, the stent 200 with the pump,and struts disposed therein, could be compressed and disposed within asheath 130 (as hereinafter discussed) and transluminally delivered asseen in FIGS. 1F and 1G, in a manner similar to and as shown asdescribed with reference to FIG. 1B. Upon removal of sheath 130 theself-expanding stent 200 with pump 10 and struts 121 would expandoutwardly as seen in FIG. 1G, similar to FIG. 1C, whereby the pump 110would be supported in a generally centrally spaced relationship from theinterior wall surface 98′ of aorta 98 or other vessel or chamber.

Preferably, the intravascular pumping module 80 of the present inventionis initially sheathed in a sheath 130 of approximately 21 French size indiameter in its undeployed configuration, as show in FIG. 1B, but othersizes are possible. The sheath size may be decreased in futureembodiments of the system. If the struts 121 are of a spring-typedesign, the sheath 130 retains the support members 121 in the desiredconfiguration illustrated in FIG. 1B. Housing 114 preferably has adiameter of approximately 18 French. The strut system, or struts 121,may also be deployed as a separate unit from the pump and initiallydeployed, and thereafter the pump 110 can then be deployed into thecenter of the strut system utilizing a locking mechanism, so that thepump may be removed and replaced at a later date so as to allow theability to replace the pump if it should fail.

With reference to FIGS. 1B and 1C, preferably, the outer end 122 of atleast one strut 121, and preferably each of the outer ends of thesupport members, or struts, 121 are provided with an anchor element,such as a small hook 123, or similar structure, which serves to anchoreach of the struts 121 at the desired location within descending aorta98 or other vessel or chamber. If desired, a plurality of anchorelements may be used.

The presence of the bypass region, or, in other words, the lack of abarrier or partition between the outlet and inlet of intravascularpumping module 80, creates a situation very different from traditionalpumping. Systems and methods for increasing fluid flow and/or augmentingpressure and/or overcoming head in a tube, pipe, vessel, container, orreservoir typically depend on pumping across a partition separating thevessel or chamber into two or more volumes. These methods typicallycontain one source of fluid that is pumped from one volume to the other.In a discrete configuration (FIG. 2A) the two volumes (2 and 6) areseparated by the pump itself. In an inline configuration (FIG. 2B), thepump is within the tube or vessel and the two volumes (12 and 18) areseparated by a partition (16) within the tube or vessel. In eitherconfiguration, the separation of the two volumes prevents the increasedflow and/or pressure at the pump outlet or discharge (10 and 22) frommoving backwards and/or inducing flow toward the pump inlet flow orsuction (8 or 20). In mechanical systems, the barrier (16) is usually amechanical valve or barrier. In biological systems, the barrier (16)could be a biological or mechanical valve or barrier (e.g. a heart valveor septum or vessel wall).

Having an open bypass around the pump allows developed pressure or flowto “slip” back around the pump and recirculate, reducing the net workcompleted. While this possibility makes effective pumping more difficultand possibly less efficient in many cases, it also enables theopportunity to increase overall flow through entrainment.

To understand the possibility the bypass path allows, consider anexample from industry (this industrial example is not an embodiment ofthe present invention). Entrainment is often used industrially (inmining, for example). Entrainment methods (FIG. 3) use a jet of fluid(24) from a source or reservoir separate from or removed from or at adistance from the suction (or upstream flow) of the pump. This jet (24)may also be termed the motive flow. The motive flow or jet (24) exitsand transfers momentum to the fluid (30) near the jet or present at thatpoint in the vessel or tube (26). This momentum transfer accelerates thevessel fluid (30). The increased velocity of the vessel fluid (30) pullsthe upstream fluid (32) along, accelerating the nearby fluid as well.This increase in vessel flow (30 and 32) by the motive flow (28) iscalled entrainment. In entrainment methods, total discharge ordownstream flow (33) equals suction or upstream flow (32) plus motiveflow (24).

Auto-entrainment (FIG. 4) describes the situation in which the flow (42and 46) in a vessel or tube (34) is accelerated by a jet or motive flow(50) that is sourced from the suction or upstream vessel flow (46). Thisis entrained in a series flow modification system analogous in anonlimiting way to the present invention. The motive flow (50) is formedby vessel flow that enters as a pump inlet flow (38), is accelerated bya pump (36), and exits as a pump outlet flow (40). The portion of theupstream flow (46) that does not flow through the pump (36) is termedbypass flow (48). In auto-entrainment, total discharge or downstreamflow (44) equals suction or upstream flow (46) equals motive flow (50)plus bypass flow (48). This differs from entrainment, where the bypassflow equals the suction flow and the motive flow is sourced separately.Effective auto-entrainment may increase flow above what the pump alonecan achieve.

In entrainment and auto-entrainment, the native flow can be described asthe flow (equal to the upstream flow and the downstream flow) presentwith no increase due to the motive flow. For the entrainmentconfiguration shown in FIG. 3, the native flow is equal to the upstreamflow (32) and equal to the downstream flow (33) when the motive flow(24) is zero. For the auto-entrainment configuration shown in FIG. 4,the native flow is equal to the upstream flow (46) and equal to thedownstream flow (44) when zero power is supplied to pump (36). Somesmall motive flow (50) may be present simply due to a portion of theupstream flow (46) moving passively through the pump (36).

In auto-entrainment, recirculation is possible under certaincircumstances (FIG. 5). In this case, the bypass flow (62) moves in theopposite direction of the upstream flow (54), downstream flow (56), andmotive flow (60) through the pump (58). As when the bypass flow is inthe same direction as the upstream and downstream flows, totaldownstream flow (56) equals upstream flow (54) equals motive flow (60)plus bypass flow (62). Total flow (equal to suction or upstream flowequal to discharge or downstream flow) may still be increased abovenative flow alone in auto-auto-entrainment with reverse bypass flow.

The following paragraphs discuss the flow and pressure modificationelements and how they can be adjusted.

The configuration of the inlet of the device may be adjusted in a numberof ways to minimize reverse bypass flow, maximize efficiency, maximizeauto-entrainment and total flow, or alter other parameters ofperformance. Among other parameters, the overall shape of the inlet endof the device as well as the size, number, shape, and location of inletports may be varied.

The inlet end of the device may comprise a “nose cone” of an arbitraryshape to modify the suction flow around and into the device. FIG. 14shows (a) flat, (b) conical, and (c) ellipsoid shaped nose cones asexamples.

As shown in FIG. 15, the basic inlet flow may be through any combinationof axial ports (172) (at the inlet end of the device) and radial ports(174) (on the side of the device). The inlet flow through both axial andradial inlet ports may be adjusted by adjusting the size, number, andlocation of the ports. FIG. 16 shows examples for a flat nose cone withaxial ports (a), a flat nose cone with radial ports (b), an ellipsoidnose cone with axial ports (c), and an ellipsoid nose cone with radialports (d). Many other combinations of these configurations are possible.FIG. 17 shows a non-symmetric, hybrid example in which inlet flow entersthrough one side of the nose cone. Such non-symmetric inlet port designmay be useful in cases where the device sits in proximity to the wall ofthe vessel or tube or reservoir.

The inlet end of the device may also comprise geometries or shapes, orinlet flow receptors (FIG. 17), one purpose of which may be to enhanceflow into the inlet ports. In one embodiment, one or more inlet flowreceptor (FIG. 17) may be provided near the inlet port to increase flowto the inlet port. The shapes utilized for inlet flow receptor mayincrease flow through the inlet ports by increasing the cross-sectionalarea of the device and directing the flow impacting such incrementalcross-sectional area into the inlet ports. Such shapes may also impactthe overall efficiency and effectiveness of the device by alteringsuction or bypass flows or pressures. FIG. 18 shows examples for axialinlet ports (b) and radial inlet ports (a, c) and non-symmetric inletports (d). Shapes like those shown in FIG. 18 may also serve to preventthe axial inlet port from coming too close to or in contact with thewall of the vessel or tube or reservoir. This may be helpful in caseswhere the vessel wall is flexible or in cases where the device has arelative wide range of motion within the vessel or tube or reservoir.

The configuration of the outlet of the device may be adjusted in anumber of ways to minimize reverse bypass flow, maximize efficiency,maximize auto-entrainment and total flow, or alter other parameters ofperformance. Among other parameters, the overall shape of the outlet endof the device as well as the size, number, shape, and location of outletports may be varied.

The outlet end of the device may comprise a “tail cone” of an arbitraryshape to modify the discharge flow path out of and around the tail endof the device. FIG. 19 shows (a) flat, (b) conical, and (c) ellipsoidshaped tail cones as examples.

As shown in FIG. 20, the basic outlet flow may be through anycombination of axial ports (196) (at the outlet end of the device) andradial ports (198) (on the side of the device). The outlet flow throughboth axial and radial outlet ports may be adjusted by adjusting thesize, number, and location of the ports. FIG. 21 shows examples for aflat tail cone with axial ports (a), a flat tail cone with radial ports(b), an ellipsoid tail cone with axial ports (c), and an ellipsoid tailcone with radial ports (d). Many other combinations of theseconfigurations are possible. FIG. 22 shows a non-symmetric, hybridexample in which outlet flow exits through one side of the tail cone.Such non-symmetric outlet port design may be useful in cases where thedevice sits in proximity to the wall of the vessel or tube or reservoir.

The outlet end of the device may also comprise geometries or shapes, oroutlet flow enhancers (FIGS. 23A to 23D), one purpose of which is toenhance flow out of the outlet ports. In one embodiment, one or moreoutlet flow enhancers (FIGS. 23A to 23D) may be provided near the outletport to increase flow to the outlet port. The shapes utilized for outletflow enhancers may enhance or modify flow through the outlet ports orthe pressure profile of such flows by modifying the path or pressureprofile of the bypass flow and changing how the outlet flow and thebypass flow interact. Further, the outlet flow enhancers may also beshaped to minimized reverse bypass flow. FIGS. 23A to 23D show examplesfor axial outlet ports (b) and radial outlet ports (a, c) andnon-symmetric outlet ports (d).

The outlet design for axial outlet ports or radial outlet ports maycomprise an outlet nozzle of any shape known in the art of jet nozzledesign. Such nozzles may be designed to enhance certain flowcharacteristics including, but not limited to, any combination ofturbulence, swirl, or particular velocity components. FIGS. 24A-I showsseveral examples for axial outlet ports with nozzles. FIG. 24a shows aconvergent nozzle. FIG. 24b shows a spike nozzle with a flow element(200) protruding from the outlet housing (202). FIG. 24c shows a bypassflow mixing nozzle. The shroud (204) captures and directs a portion ofthe bypass flow (206) toward the outlet port (216) of the outlet housing(208), enhancing the mixing of the bypass flow (206) and the outlet flow(or motive flow) (210) and thereby altering the interaction of theoutlet flow and the bypass flow and the resultant flow and pressureprofiles. FIG. 24d shows a laminar flow nozzle comprising a flowstraightener (214) and an outlet orifice plate (212). The outlet orificeplate (212) may have any number of outlet ports of any shape. The flowstraightener (214) may comprise elements that serve to enhance swirl oradd skew components to the outlet velocity. FIG. 24e and FIG. 24f eachshow an example of an indeterminate origin (or IO) nozzle. FIGS. 24g -1and 24 g-2 shows two views of an inducement nozzle that draws the nativeflow into the center of the lumen, surrounded by outlet jets. FIG. 24hshows a swirl reducing flow straightener. FIG. 24i shows a swirlreducing straightening nozzle. In any of these embodiments, the goal maybe to adjust or modify the width, angle, shape, swirl, turbulence, orother attributes of the outlet jet or its mixing with the bypass flow,independently or in combination. Radial outlet ports may also comprisenozzles of any arbitrary type. Elements like diffusers or porous mediawith certain characteristics may also be used to condition flow andpressure upstream or downstream of the nozzle.

Embodiments designed for enhancing circulation or perfusion may also usenozzles as discussed in connection with FIGS. 24A-I to alter or augmentor enhance or control the flow and pressure changes created by thedevice.

In one set of embodiments (illustrated in FIG. 33), the configuration ofoutlet flow ports is adjusted to enhance kidney perfusion by selectivelyincreasing flow and pressure to the renal arteries

Various nozzle designs shown in the figures generate confined, laminarflow.

Outlets promoting/reducing swirl may be provided.

In certain embodiments, the device may contain one or more flowdirectors that serve to modify the direction or velocity or otherparameter of the motive flow as it enters the device, travels throughthe device, or exits the device. FIGS. 25a-25g shows several examples ofsuch flow directors. Flow directors that modify flow into (e.g., FIG. 10(102)) or out of (e.g., FIG. 10 (106)) the device may be referred to as“flow-around” flow directors and flow directors that modify flow throughthe device (e.g., FIG. 10 (104)) may be referred to as “flow-through”flow directors.

FIG. 25a shows a flow-around flow director (188) as an element of theinlet housing (190). FIG. 25b shows a flow-around flow director (192) asan element of the outlet housing (194). A flow-around flow director mayhave any arbitrary shape. FIG. 25c shows a flow-around flow directorthat is a solid of revolution.

Flow directors may comprise elements that serve to modify selectivecomponents of the motive flow. For example, flow directors may havevanes to reduce or eliminate radial components of motive flow velocity.In other embodiments, the vanes may be formed into a spiral or corkscrewshape in order to impart radial components to the motive flow velocity.FIGS. 25d -1 and 25 d-2 shows two views of a flow-around flow directorwith a two vanes (218) built into the solid of revolution (220). FIG.25e shows a flow-around flow director with four vanes (222) built intothe solid of revolution (224). In general, a flow director may have anynumber of vanes with regular or irregular spacing between those vanes.

FIG. 25f shows a four vane flow-through flow director. FIG. 25g shows athree vane flow-through flow director. In general, a flow director mayhave any number of vanes with regular or irregular spacing between thosevanes. A flow-through flow director may also comprise elements creatingany number of distinct flow paths that remain independent orinterconnect with one another. The flow straightener (214) shown in FIG.24d is an example of such a flow-through flow director comprisingelements creating a large number of independent distinct flow paths.These flow paths may be designed to adjust, modify, augment, change,impart, enhance, reduce, or eliminate certain axial or radial or skewvelocity components of the motive flow.

Flow directors may also have some characteristics of jet nozzlesincluding, but not limited to, diameters that vary with longitudinaldistance (e.g. convergent or divergent sections) or sections withindeterminate origin or irregular circumferences.

In some embodiments, the struts or other support mechanisms may alsoserve to direct, restrict, block, occlude, and/or otherwise modify thebypass flow and may have special shapes or features for that purpose.

Any flow director that extends beyond the basic diameter or length ofthe device can have pre- and post-deployment configurations. Deploymentcan be due to spring constant or shape memory with heat or current. Onenonlimiting example of this is a one-way valve designed to preventrecirculation through the bypass region and described relative to theintravascular pumping module for simplicity.

With reference to FIG. 1E, a figure similar to FIG. 1C, theintravascular pumping module 80 is provided with a one-way valve 170,and is shown disposed in the descending aorta 98 or other vessel orchamber. The same reference numerals are used for the same componentsshown and described in connection with FIGS. 1B and 1C. One-way valve170 may be provided to prevent backflow of blood 81″ from flowingupwardly through the bypass region back into descending aorta 98 orother vessel or chamber. One-way valve 170 may be provided in anysuitable manner, such as by supporting one-way valve 170 by a strutsystem 171 associated with housing 114. Strut system 171 may include aplurality of strut members 172 which may be deployed in a similar mannerto strut members 121 of strut system 120 to bring the circumferentialend, or lip, 172 of one-way valve 170 into a sealing relationship withthe interior surface 98′ of descending aorta 98 or other vessel orchamber or other vessel or chamber. The other, smaller diametercircumferential end, or lip, 174 of one-way valve 170 is shown in FIG.1E disposed in its sealed relationship with respect to housing 114,whereby backflow of blood 81″ upwardly into descending aorta 98 or othervessel or chamber is prevented. As blood 81″ is pumped to flowdownwardly into descending aorta 98 or other vessel or chamber, one-wayvalve 170 may open as shown by dotted lines 170′, whereby one-way valve170 opens as shown in the direction of arrows 175, whereby thecircumferential lip 174 of one-way valve 170 moves outwardly fromhousing 114 to permit blood 81″ to flow not only through pump 110, butalso through bypass region in the normal direction of native flow andinto descending aorta 98 or other vessel or chamber.

One-way valve 170 may be made of any suitable bio-compatible, orbiomaterial, including plastic materials, having the requisite strengthand bio-compatibility characteristics which permit the desired use in aperson's aorta or other vessel or chamber and permits the function ofone-way valve 170. Rigid biomaterials or flexible biomaterials may beutilized for the construction of one-way valve 170.

In addition to the design and location of the inlets, outlets, and flowdirectors, several physical dimensions (FIG. 7) of the pump can bevaried to minimize reverse bypass flow, maximize efficiency, or maximizeauto-entrainment and total flow. The overall length (68) between inletports (64) and outlet ports (66) of the pump can be changed. Longerlengths (68) provide for a higher bypass volume with more kinetic energycontained in the bypass flow (126) making it more difficult to reverseflow direction. Longer lengths (68) also cause more resistance to thebypass flow (126), reducing its energy and making it easier to reverseflow direction. Whether the net effect is to make reverse bypass flowmore or less likely depends on the specific fluid in question and thespecific geometry of the bypass path. The specific geometry of thebypass path, or the fluid pathway bypassing the pump (128), depends onthe height (72) of the bypass path and the position or orientation orconfiguration of the pump (128) within the tube or vessel (130) asdiscussed in connection with FIG. 6 below. The bypass height (thethickness of the bypass annulus) is the diameter of the vessel (130)minus the diameter (70) of the pump (128).

Adjusting Physical Dimensions: All the physical dimensions of the devicemay be varied to enhance or modify or target or limit or controlpressure and flow in the region of the pump. The description above inconnection with FIG. 7 discusses many of these physical dimensions orparameters.

Referring to FIG. 7, the overall length (68) between inlet ports (64)and outlet ports (66) of the pump can be adjusted to differentiallyaugment flow to vessels up and downstream of the renal arteries. Thediameter (70) of the device (128) can also be varied to affect bypassflow (126) and the flow and pressure profiles around the pump. Thediameter (70) of the device (128) may also be made to vary along thelength of the device such that the device has an arbitrary profile. Incertain embodiments, the diameter of some part of the device may belarge enough to effectively reduce or minimize bypass flow in the vesselthe device sits in. This may be due to the minimum required diameter ofthe device in smaller vessels or due to a portion of the device designedto have a large diameter in larger vessels.

In embodiments where the device sits against vessel wall, the shape ofthe device may not be symmetric around the longitudinal axis of thedevice. For example, one portion of the device may be shaped to fitagainst the vessel wall while the portion of the device away from thewall of the vessel may have an arbitrary shape.

In embodiments with more than one pump or cannula or inlet or outlet,the size and shape of each segment or component or part or aspect of thedevice can be individually varied or adjusted.

The position or orientation (FIG. 6) of the device within the vessel ortube or reservoir can be varied to minimize reverse bypass flow,maximize efficiency, maximize auto-entrainment and total flow, or alterother parameters of performance. In general, three orientationparameters (e.g. roll (176), pitch (178), and yaw (180) as shown in FIG.6a ) and three location parameters (e.g. distances along threeorthogonal axes from some reference point or origin, e.g. longitudinal(182), horizontal (184), and vertical (186) as shown in FIG. 6b ) can beadjusted alone or in combination. Both location and orientation can berepresented in any number of other coordinate systems.

In certain embodiments and implementations, the efficiency andeffectiveness of the intravascular pumping module may depend on theposition and orientation of the device relative to some anatomicalfeature or branch vessel of the vessel or chamber the device is locatedin. In such cases, the proximity or location and orientation of thedevice relative to the anatomical feature or branch vessel of the vesselor chamber can be specified using the coordinate systems described inFIG. 6 or some other coordinate system.

In practice, the device will simply be imaged and manipulated until itis in the correct position and orientation.

In embodiments in which the device is within a vessel or chamber ofapproximately cylindrical shape, some of the basic orientations includeaxiosymmetric, axis-parallel, axis-intersecting, and skew (FIGS. 12A-1to 12D-2). In an axiosymmetric embodiment (FIGS. 12a -1 and 12 a-2), thelongitudinal axis (132) of the vessel or chamber (134) and thelongitudinal axis (136) of the device (138) are the same. In otherwords, the tube (134) and device (138) share the same axis passingthrough the center of each. In an axis-parallel embodiment (FIGS. 12b -1and 12 b-2), the longitudinal axis (146) of the device (144) is parallelto the longitudinal axis (142) of the vessel or chamber (140). Theperpendicular distance between the two axes can be varied from zero (anaxiosymmetric embodiment) to roughly the radius of the vessel or chamber(at which point the device is against the wall of the vessel orchamber). In an axis-intersecting embodiment (FIGS. 12c -1 and 12 c-2),the longitudinal axis (150) of the device (152) intersects thelongitudinal axis (148) of the vessel or chamber (156) at a point (154),so the longitudinal axis (150) of the device (152) and the longitudinalaxis (148) of the vessel or chamber (156) lie in the same plane. Assuch, the axes are not parallel and intersect. While the axes intersect,the device (152) itself may or may not intersect the longitudinal axis(148) of the vessel or chamber (156). In the embodiments where thedevice itself does not intersect the longitudinal axis (148) of thevessel or chamber, the axes intersect at a point (154) away from device(152). In a skew embodiment (FIGS. 12d -1 and 12 d-2), the longitudinalaxis (162) of the device (160) and the longitudinal axis (164) of thevessel or chamber (158) do not lie in the same plane. As such, the axesare not parallel and do not intersect.

In the body, the assumption of the vessel or chamber being a straightcylinder will only be approximate. In these cases, the positions andorientations described in FIGS. 12A-1 to 12D-2 may serve as descriptionsof the approximate or nominal or desired or intended position ororientation.

Given a particular orientation (including, but not limited to, thosedescribed in connection with FIGS. 12A-1 to 12D-2), defining thethree-dimensional location of any part of the device (e.g. its center,inlet, or outlet) fully defines its complete position and orientation.In certain embodiments, the three dimensional location of a referencepart of the device may be specified by how far the device is locatedfrom a particular collateral vessel or bifurcation or valve or narrowingor bend or other change in the biological vessel. For example, thethree-dimensional location of a reference part of the device may bespecified by its distance from the aortic valve or the aortic arch orthe renal arteries or the iliac bifurcation or any other such biologicallandmarks.

Adjusting Position and Orientation of Multiple Components. Inembodiments in which the device comprises one or more flexible cannulas,the position or orientation of each rigid section can be independentlyadjusted. FIG. 13 shows an embodiment with an axis-parallel component(166) and an axis-intersecting component (168) connected by a flexiblecannula (170)

An embodiment of the present invention for enhancing circulation orperfusion may comprise any number of pumps or cannulas or inlets oroutlets. Examples of some multi-pump configurations are shown in FIG.26. Multiple pumps may be useful for increasing or enhancing circulationor perfusion beyond what a single pump is capable of, providing the samepower or motive flow in a small diameter (by using multiple smallerdiameter pumps to match the power of a single, larger diameter pump), orbetter localizing the region of augmented pressure or flow. FIG. 32illustrates how two pumps could be combined to create a limited area ofhigher pressure with minimal effects to other areas.

Additionally, two or more pumps 110, 110′ may be placed in series or inparallel in the descending aorta with one pump being designed in a morecranial position and the other pump in a more caudal position, so as toallow for redundancy of the pumps in case one fails and to allow formore pumping capability while utilizing the same French size sheath fordelivery, as shown in FIG. 1D. In some embodiments, the one or morepumps may be aligned so that the outlet of one pump feeds the inlet ofanother pump. In some embodiments, the outlet of a first pump may bepositioned next to the inlet of second pump with the outlet of the firstpump being offset from the inlet of the second pump. In someembodiments, the outlet of a first pump may be positioned to face theoutlet of a second pump. In some embodiments, the inlet of a first pumpmay be positioned to face the inlet of a second pump.

In general, any number of motors, impellers, and cannulas can beconnected in series or in parallel together to create a single device.FIG. 26A-26D shows three examples of embodiments with multiple motors orpumps or cannulas. FIG. 26 shows combinations of the embodiment of thedevice described in FIG. 10 to illustrate some basic configurations.Many other configurations and combinations are possible and useful andmay not require all of the device components shown in FIG. 10 or maycontain additional components. The configurations shown in FIGS. 26 a,b, c, and d (and, in general, any configuration) may instead functionwith flow reversed from the flow direction indicated.

FIG. 26a shows two instances (226 and 228) of a basic device embodimentconnected by a tether (236). The tether (236) may be a power line orelectrical wire or electrical cable. Outlet flow from the first device(226) mixes with the bypass flow. This configuration may be extended toany number of instances of the device. FIG. 26b shows two instances (230and 232) of a pump portion of a basic device embodiment connected by acommon flexible cannula (234). In this configuration, the ports of onepump unit (230) function as inlet ports and the ports of one pump unit(232) function as outlet ports. Further, the outlet flow from the firstdevice (230) does not mix with the bypass flow before reaching seconddevice (232). FIG. 26c shows three instances (238, 240, and 242) of abasic device embodiment. The outlet housing or flow director of instance(238) is connected to the motor of instance (240) and the outlet housingor flow director of instance (240) is connected to the motor of instance(242). Outlet flow from the devices (238, 240) mix with the bypass flow.This configuration may be extended to any number of instances of thedevice. FIG. 26d shows two instances (244 and 246) of a basic deviceembodiment joined as described in FIG. 26c with the addition of a flowconfiner (248). The flow confiner (248) allows the outlet flow of device(244) to flow to the inlet of device (246) without mixing with thebypass flow. This configuration may be extended to any number ofinstances of the device. In some embodiments, the flow confiner (248)may be fashioned from collapsible material so that it increases thediameter of the device only minimally when collapsed. In otherembodiments, the diameter of the flow confiner (248) may be reduced byreducing the diameter of the motor of device (246).

The dynamic performance of the circulation and perfusion enhancementsystem will depend on the configuration location parameters discussedabove and on the motive hemodynamic power supplied by the intravascularpump module(s). The power levels required for certain performance levelsmay be estimated by considering a number of factors including thedesired pressure and flow changes (based in part on the condition beingtreated), the volume and location of the region where the pressure andflow changes are desired, the native flow and resistance to flow in thatregion, or the number of pumps deployed. In practice, estimates ofrequired power will typically be refined by simulation and experiment.The determination of required pump power may consider the maximum pumppower required, since the applied power may be controllable andreducible to provide lower power levels when desired.

The paragraphs above have described the major parameters of thecirculation and perfusion enhancement system: flow and pressuremodification elements (inlets, outlets, and flow directors), systemdimensions, location and orientation, number and arrangement of pumps,and pump power levels. The next step is to specify these parameters togenerate flow and pressure effects that, in turn, drive circulation andpressure enhancements specifically designed to treat a particularconditions or disease state. One aspect of generating desired flow andpressure effects is designing parameter sets that produce theappropriate flow patterns in the bypass region. What this pattern shouldbe will depend on the particular embodiment and indication, but threecommon targeted flow patterns are allowing recirculation, maximizingauto-entrainment, and creating a “fluid dynamic valve”. Recirculation(reverse bypass flow) when the outlet effects are high pressure, low netflow, and low swirl. These conditions can be achieved with an annularoutput nozzle that develops radial flow. In contrast, in otherembodiments, it is desirable to achieve maximal total flow orefficiency. In these cases generating stable auto-entrainment isdesirable. The optimal parameter set to generate auto-entrainment willdepend on the particular embodiment and hemodynamics, but a commoncombination is a high velocity laminar flow maximally down the lumen ofthe artery together with a restricted or staggered inlet. The inletdesign encourages flow into the bypass region and the high velocityoutlet jets generate low pressure areas that draw flow from out of thebypass region. Additionally, the central laminar flow can continue toentrain flow at some distance from the outlet through laminar velocityshear. Alternatively, nonlaminar flow directed at a slight angle to theaxis of the vessel can entrain flow from the bypass region throughturbulent diffusion of momentum. In yet other embodiments,auto-entrainment may be undesirable or unattainable and an appropriateflow pattern for the bypass region is a fluid dynamic valve. This is aflow pattern that prevents recirculation but has essentially zero netflow. A standing swirl (circumferential velocity) is a common example.

This simple and nonlimiting perspective on possible flow patterns in thebypass region is enough to develop parameter sets for treatingparticular conditions or disease states by targeting specific (i.e.magnitude and location) circulation and perfusion enhancements.

Conditions in which targeted, localized, short-term or long-termcirculation improvement may be desirable or beneficial may include, butare not limited to: heart failure (assist in moving blood away from theheart), compartment syndrome (reduce flow to allow pressure drop inaffected area), kidney issues and complaints including AKI, sepsis,shock (including cariogenic shock, hypovolemic shock, and hemorrhagicshock), Raynaud's phenomenon, poor peripheral circulation (peripheralvascular disease), chronic venous insufficiency (edema), poor perfusionof the small or large intestines or conditions possibly resulting fromsuch poor perfusion, hypervolemia (possibly to increase kidneyfunction), hypovolemia (to maintain perfusion of key organs),tachycardia/bradycardia (through regulation of afterload and aorticpressure), poor circulation due to obesity, peripheral neuropathiescaused diabetes mellitus or other causes, cystic fibrosis, or fluid inthe lungs

Embodiments of the present invention may be used to increase or enhancecirculation or renal (or other end-organ) perfusion for short-term orlong-term durations. Embodiments of the present invention used toenhance circulation or perfusion may or may not use or include orrepresent all aspects or characteristics of the present invention. Forexample, in some cases, the diameter of the device may be roughlyequivalent to the blood vessel the device is located in. In such cases,bypass flow and auto-entrainment may be less important whereas othercharacteristics or aspects of the current invention, such as axial inletand outlet port design, will be more important to achieving sufficientenhancement to circulation or perfusion.

For many embodiments of the circulation and perfusion enhancement systemtargeting treatment of many different disease states, developing asuitable parameter set (including, for example, but not limited to,determining the nozzle designs and power levels that provide thegreatest net flow under various native flow and pressure profiles) willbe an iterative process involving computational fluid dynamics, in-vitrosimulations, animal experiments, and controlled human clinical trials.The availability of data from these simulations and experiments, alongwith evolving ideas from clinicians and researchers about what the mostdesirable circulation and perfusion enhancements for treating variousconditions or disease states, will build better information about theuse of the present invention to provide those treatments. The currentlypresented parameter sets, flow and pressure effects, and circulation andperfusion enhancements listed for each condition below are nonlimitingexamples of basic approaches.

Summary Example Embodiments for Various Diseases Conditions

The conditions provide a mix of chronic and acute conditions that wouldhave a range of treatment durations from several hours to severalmonths. The paragraphs below describe example embodiments of theintravascular pumping module using one pump. These example embodimentsdiscuss specific implantation locations, but it will be clear to thoseof ordinary skill in the art that a range of locations will be suitablein each case, that if the described locations are for some reasonunsuitable, other locations can be used, and that the flow and pressuremodification elements of the present invention can be used from a broadrange of potential implantation locations to gain greater or morespecific improvements in circulation or perfusion in the region ofinterest than a blood pump designed for non-specific systemiccirculation enhancement would provide. Additionally, effectiveness ofthese treatments does not depend on matching all system parameters. Forexample, substantially increased net flow can be can be generatedwithout auto-entrainment and without swirl reduction. Substantialimprovement over non-specific systemic circulation enhancement isachievable through coarse adjustment of just the basic parameters ofoutlet flow direction and velocity. Finer adjustment of those or otherparameters can increase the effectiveness and efficiency of theintravascular pumping module.

Note that those of ordinary skill in the art may have differing opinionsof what specific circulation and perfusion enhancements would providethe most effective treatment for a particular condition. These opinionsmay change over time as new studies and research provide new data. Theexamples below are not meant to be limiting in any way, but rather todemonstrate the flexibility of the intravascular pumping module inproviding whatever specific circulation and perfusion enhancements aredesired.

The first example embodiment, for treating heart failure, will beexplored in detail to illustrate how the flexibility and configurabilityof the circulation and perfusion enhancement system can generate thespecific circulation and perfusion enhancements identified.

Heart Failure:

One dimension of heart failure is unloading of the left ventricle torest the heart. This treatment approach can be thought of as essentiallyreducing the systemic vascular resistance that the heart pumps against.Such unloading also treats the related conditions of pulmonary venoushypertension and cardiogenic pulmonary edema.

In one approach to resting the heart as much as possible, the desiredeffects of the circulation and perfusion enhancement system are maximalnet flow increase in the aorta (to assist the heart in moving bloodaround the body) and reduced aortic root pressure (to reduce thepressure the heart ejects blood against during systole). Note that VADs(whether traditional, less-invasive, or percutaneous) assist incirculation but typically increase pressure in the aortic root. Othertreatments, like inter-atrial shunts, reduce pre-load but not aorticpressure.

To assist general systemic circulation, the circulation and perfusionenhancement should be placed in the aorta before major branch vesselsdivide the flow. This consideration suggests placement above the celiacartery. The pressure drop upstream of the device increases as the volumeof blood upstream of the device decreases. For this reason, placing thedevice closer to the aortic root generates greater pressure drops in theaortic root.

In a particular embodiment, consideration of a number of factors mightlead to a placement in the descending thoracic aorta behind the heartand above the diaphragm: first, placement downstream of the carotidartery branches virtually eliminates risk of a stroke caused by thedevice; second, sufficient blood volume upstream of the device should bemaintained so as to not drop aortic root pressure too low; third, theoutlet flow of the device can be better directed once the aortastraightens after the aortic arch.

To encourage high net flow, the outlet of the circulation and perfusionenhancement device should have high auto-entrainment and lowrecirculation in the bypass region and direct its outlet flow along thedirection of native flow with low swirl. These factors are consistentwith configuring the device outlet to produce a laminar or lowturbulence jet directed along the axis of the aorta. This impartsmomentum in the direction of native flow without the circumferentialflow component of swirl, reduces the possibility of recirculation bymoving pumped blood away as fast as possible, and encouragesauto-entrainment through shear between the outlet jet and thesurrounding native flow.

In summary, to generate the desired effects in this potentialembodiment, the circulation and perfusion enhancement system is orientedfor downward flow in the thoracic aorta with the outlet at above thediaphragm at T6-T8. The flow control elements are configured to producemaximally downstream (i.e. in direction of native flow) flow with lowturbulence, auto-entrainment, and minimal downstream swirl. The durationof this treatment may last from one to six months. A similar circulationand perfusion enhancement, but for hours instead of months, may bebeneficial in providing cardiac support and unloading to post myocardialinfarction or post cardiac surgery patients. One potential benefit ofthe circulation and perfusion enhancement discussed is the reduction inaortic root pressure with preserved flow. This reduced pressure couldhelp prevent or reduce reperfusion injuries to the heart during itsrecovery period.

The above examples give an indication of how the circulation andperfusion enhancement system can be configured to produce very specificeffects. None of that discussion (or the discussion below) should betaken as limiting the potential of the circulation and perfusionenhancement system from being used to generate any possible circulationor perfusion enhancement for any disease or condition from any possibleimplantation site.

In the following example embodiments, the discussion for each disease orcondition begins with an assumption of the specific effects desired fromthe intravascular pumping module.

Kidney Dysfunction:

The assumed desired effect in this example embodiment is increasedpressure at renal branching. To generate this effect, the circulationand perfusion enhancement system is oriented for downward flow in theabdominal aorta with outlet just above both renal branches (T12-L1). Theflow control elements are configured to produce high radial flow and noauto-entrainment. Note that “leakage” of the high pressure region mayresult in increases in peripheral circulation (downward leakage) oraortic root pressure (upward leakage); this can be mitigated, if desiredor necessary, with a two pump solution. The duration of this treatmentmay last anywhere from several hours to several months depending on theunderlying condition. A similar circulation and perfusion enhancement,but may be beneficial in providing kidney support during surgicalprocedures using cardiopulmonary bypass. A significant fraction of suchprocedures lead to serious kidney injuries and need for dialysis. It ispossible that enhanced kidney perfusion during and following theprocedure could reduce this risk (potentially by lowering pressures atcertain points to prevent reperfusion injuries).

Cardio-Renal Syndrome:

The assumed desired effects in this example embodiment are reducedaortic root pressure and net flow increase together with increasedpressure at renal branching (compromise between heart failure and kidneydysfunction treatments). To generate these effects, the circulation andperfusion enhancement system is oriented for downward flow in aortabetween arch and renal branching (outlet at T9-T10). The flow controlelements are configured to produce 45 degree flow with fluid dynamicvalve to minimize recirculation, reduced downstream swirl. Note that theextension of high pressure region past branching area may result inincreases in peripheral circulation; this can be mitigated, if desiredor necessary, with a two pump solution.

Endothelial Dysfunction:

The assumed desired effects in this example embodiment are net flowincrease with high swirl. To generate these effects, the circulation andperfusion enhancement system is oriented for downward flow in thoracicaorta at/above diaphragm (outlet at T6-T8). The flow control elementsare configured to produce maximal swirl downstream of outlet with noreduction in net flow.

Sepsis:

The assumed desired effects in this example embodiment are increased endorgan perfusion with reduced peripheral circulation. To generate theseeffects, the circulation and perfusion enhancement system is orientedfor upward flow just above aortic bifurcation. The flow control elementsare configured to produce maximally upstream flow (i.e oppositedirection of native flow) with minimal swirl. Note that the extension ofhigh pressure region upstream may result in increases in aortic rootpressure; this can be mitigated, if desired or necessary, with a twopump solution.

Aneurysm:

The assumed desired effects in this example embodiment are focusedpressure reduction in region of aneurysm or other aortic defect, withthe system positioned away from the aneurysm or defect. To generatethese effects, the circulation and perfusion enhancement system isfitted with an outflow cannula, oriented to discharge in the directionof native flow, and positioned upstream of the aneurysm or defect withthe outflow cannula extending through to the downstream side of theaneurysm or defect. The flow control elements are configured formoderate flows and minimal downstream swirl.

The above nonlimiting examples illustrate the novel benefits of thecirculation and perfusion enhancement system. Further examples will bedescribed more briefly.

Peripheral Vascular Disease may respond to embodiments that place thepumping modules in the iliac arteries or at the base of the aorta,configured to raise pressure and flow in the leg arteries.

The circulation and perfusion enhancement system could be placed andconfigured for wound healing or post surgical support by targeting majorsupply arteries to the surgical site. A nonlimiting examples of thisinclude creating perfusion changes in the iliac artery for a leg injuryor in the celiac artery for liver surgery. The treatment may involvedecreased perfusion initially to prevent inflammation and reperfusioninjuries and increased perfusion later to promote healing and cellgrowth. Similar approaches could increase perfusion to the same areas totreat non-specific or idiopathic injuries.

The circulation and perfusion enhancement system could provide perfusionchanges directed toward particular end-organs (or even parts ofparticular end-organs through placement in the celiac, SMA, IMA, orgonadal arteries) and coordinated with chemotherapy or other cancertreatments to improve efficacy or reduce side effects. For blood bornechemotherapeutics, perfusion of susceptible organs could be reduced.Alternatively, perfusion of the tumor could be reduced to enhance othertreatments.

The circulation and perfusion enhancement system could be configured toproduce small and controlled reductions in flow and pressure in theceliac artery that may promote weight loss. This active and controllableapproach may be superior to a static obstruction which, if toorestrictive, could lead to tissue death.

The circulation and perfusion enhancement system can provide key regionsof the body with relief from chronic hypertension. As a nonlimitingexample, the example embodiment discussed above in connection with heartfailure reduces blood pressure in the carotids, coronaries, and aorticroot—all key risk areas susceptible to high blood pressure. Reducingpressure in these areas (even by increasing it in other regions) couldpotentially decrease the severity of the underlying hypertension.

The circulation and perfusion enhancement system could be located in thepulmonary artery to increase blood flow through the lungs and reduceeffective pulmonary vascular resistance. This embodiment may provide aneffective treatment for pulmonary arterial hypertension and help preventright heart failure. This placement would require the power wire tocross the tricuspid and pulmonary valves.

Note that many diseases or conditions occur in combination and arethought to be inter-related. One example is heart failure and kidneydysfunction, the combination of which is sometimes referred to ascariorenal syndrome. It will be apparent to one of ordinary skill in theart that system parameters can be adjusted to provide a mix of thedesired effects for treating each condition.

Many variations of these example embodiments are possible including, butnot limited to, changing the orientation of the pumping module in radialflow cases, using additional pumps, changing power levels, or makingsmall changes in various other parameters.

Methods of Providing Disease or Condition Appropriate Therapy

The major steps in using embodiments of the present invention to enhancecirculation or perfusion by altering or augmenting or enhancing pressureand flow are: Step 1) Select the appropriate class of device for thecondition being treated and the targeted or desired pressure and flowaugmentation. Step 2) Select the appropriate size and make finaladjustments based on patient specific factors. Step 3) Locate and Orientthe Device. Step 4) Operate the Device. Step 5) Remove the device. Thesesteps are discussed more fully below.

Step 1: Select the appropriate class of device for the condition beingtreated and the targeted or desired pressure and flow augmentation

Step 2: Select the appropriate size and make final adjustments based onpatient specific factors

Step 3a: Implantation alternative 1. The method or procedure totransluminally implant the intravascular pumping module 80 of thepresent invention may include some, or all, of the following steps.First, the patient is prepared in a catheterization lab in a standardfashion. Under conscious sedation, local anesthesia is applied to thefemoral area, similar to the manner in which a standard heartcatheterization is performed. A small 3 cm incision is made in thevertical plane overlying the femoral artery 10, just below the inguinalligament. The femoral artery is exposed, and may then be entered by theSeldinger technique over a guide-wire and is successively dilated toallow entry of a sheath 140, having a preferred diameter of 21 French(FIG. 1B). The sheath 140 is then passed over a guide-wire and thenplaced into position in the descending aorta 98 or other vessel orchamber, with the tip 141 (FIG. 1B) in the mid thoracic aorta, superiorto splanchnic arteries. The sheath 140 is then de-aired. Sheath 140contains at its external end, outside the patient's body, a one-wayvalve and a side arm for de-airing. The intravascular pumping module 80is then passed through the one-way valve into the sheath 140 to the tip141 at the mid thoracic area. The passage of the intravascular pumpingmodule 80 through the sheath 140 is made possible with an obturator (notshown). As the obturator is held in place, the sheath 130 is thenwithdrawn, which in the case of a spring type support structure 120, thesupport members, or struts 121 then spring open and anchor the pump 110in the descending aorta 98 or other vessel or chamber, or alternatively,if support structure 120 is a self-expanding stent 200, stent 200springs open and anchors the pump 110 in the aorta 98 or other vessel orchamber. The obturator is then removed, and the sheath 140 is thenpulled back with the power wire 117 still passing through, or disposedwithin, the sheath 140. Power can then be applied to the power wire,either directly or through the controller, to begin operation.Subclavian approach: Alternatively, rather than transluminallyimplanting the intravascular pumping module 80 of the present inventionthrough the femoral artery, as previously described, intravascularpumping module 80 may be transluminally implanted and delivered throughthe left or right subclavian artery, and the power source or battery andcontroller may be placed in the pectoral area of the patient. This typeof implant technique would be similar to the implantation of a cardiacpacemaker or defibrillator, with the exception that access would beobtained through the subclavian artery, rather than the subclavian vein.The power source, and/or its controller, may be incorporated in a devicesuch as a cardiac pacemaker or defibrillator, if used in this manner.The implantation method discussed above is provided for illustrativepurpose only. It will be recognized by one of ordinary skill in the artthat the intravascular pumping module 80 may be implanted in otherlocations utilizing any suitable implantation method known.

Step 3: Implantation alternative 2. Prior to the implantation procedure,examine the patient and use externally observable anatomical landmarksto estimate the desired position of the device. Place one or moreadhesive radiopaque markers on the body so that the desired position ofthe device can be observed by fluoroscopy. For example, place markers onboth sides of the body so that a line drawn between them passes throughthe estimated required position of the device. In this example, thedesired position of the device will appear in between the two markers.Place the patient in the cath-lab and follow standard procedures to prepthe patient for a catheter procedure. Using standard cath-lab techniquesand standard access sites for the target vessel or chamber, advance aguidewire through the appropriate vessels or chambers to or past theestimated implantation site as marked by the externally affixedradiopaque markers. Using imaging (e.g. dye and fluoroscopy,intravascular ultrasound) measure the diameter of the vessel or chamberat the implantation site to verify allowable device dimensions. Preparea device with the appropriate hemodynamic features and dimensions. Thedevice is placed in its pre-deployment configuration inside one end of asheath long enough for the other end to remain outside the body when thedevice is advanced to its implantation site. The sheath contains anobturator that reaches the end of the device and extends out of thesheath on the other side. The devices power wire and a snare wire extendfrom the end of the device, through and past the end of the obturator.The power wire is connected to the device. The snare wire is enclosed onthe retrieval hook or slot at the end of the device. Assembly of thesedelivery packages for a number of devices with a range of dimensions maytake place well in advance of the procedure. Using standard cath-labtechniques, including dilators and introducers, to provide large boreaccess at the access site. Using standard cath-lab techniques, introducethe entire delivery package (device, sheath, obturator, power wire, andsnare wire) into the vessel at the access site with no relative motionbetween the components of the delivery package. Advance the entiredelivery package, with no relative motion of the components, until thedevice sits at its intended implantation site as determined by thealignment of the device and the external radiopaque markers as observedby fluoroscopy. While holding the obturator in place to maintain deviceposition, pull the sheath slowly out of the vessel until the struts andany other collapsed features are exposed and in their expandeddeployment position. Verify the deployed position of the device and itsstruts by fluoroscopy. If the deployment is not satisfactory, hold thedevice in place by tension on the snare wire and advance the sheath tocollapse the struts back to their pre-deployment configuration. Oncethis is complete, the device can be repositioned and redeployed by onceagain pulling the sheath back away from the device. Once the deployedposition of the device and its struts is verified, release the snarewire from the retrieval hook or feature and withdraw it through theobturator. Withdraw the obturator and sheath completely. Close thevessel access with standard cath-lab techniques for large bore devices.If desired, for longer treatment durations (over seven days), animplantable electronics package may be used. In this case, tunnel thepower wire under the skin to the approximate desired site of theimplantable electronics package. Options: Guidewire is optional. Entireprocedure could take place without fluoro, at least for simplerimplantations like in the aorta. The radiopaque markers are optional.Observable anatomic markers (like the diaphragm) or ad hoc markers (likesurgical tools set on the patient's body) could be used instead. Snarewire is optional. The power wire could be made strong enough to be usedinstead or the device could be implanted with no immediate option forre-sheathing. In this last case, the retrieval process could be followedif retrieval or repositioning is needed.

Step 3b: Implantation alternative 2. Locate and orient the device forthe condition being treated and the targeted or desired pressure andflow augmentation. To achieve series flow and/or pressure augmentationthrough auto-entrainment, the device is placed within the vessel orchamber in the proper location and orientation. Localizing or limitingor targeting or focusing the augmented blood flow and blood pressure toone organ or region or area of the body may be useful to achieve desiredenhancements in circulation and perfusion in one area of the bodywithout unnecessarily impacting other areas of the body. One set ofmajor factors in such localizing or limiting or targeting or focusingincludes adjusting pump location or position or orientation within thevasculature or blood vessel. The changes to flow or pressure in a bloodvessel or vessels created by the device (and therefore the enhancementto circulation or perfusion) may be adjusted or modified or impacted byaltering the location of the device within the vasculature orcirculatory system or by altering the position and orientation of thedevice within a particular blood vessel. In general, and as discussed inconnection with FIG. 6, any of three orientation parameters (e.g. roll,pitch, and yaw) or any of three location parameters (e.g. distancesalong three orthogonal axes from some reference point or origin) may beadjusted alone or in combination. Examples of some of the basicorientations that may be used for enhancing circulation or perfusion byaltering or augmenting or changing flow and pressure are discussed inconnection with FIG. 12. Given a particular pump orientation (including,but not limited to, those described in connection with FIG. 12),specifying the three-dimensional location of any part of the device(e.g. its center, inlet, or outlet) fully defines its complete positionand orientation. In embodiments meant to enhance circulation orperfusion of some region of the body, the three-dimensional location ofa reference part of the device may be specified by how far that part ofthe device is located from a particular collateral vessel or bifurcationor valve or narrowing or bend or other change or feature or landmark ofthe circulatory system. For example, the three-dimensional location of areference part of the device may be specified by its distance from theaortic valve or the aortic arch or the renal arteries or the iliacbifurcation or any other such biological landmarks. The landmarks usedand the desired distances from those landmarks may depend on the designof the device, the condition being treated with enhanced circulation orperfusion, and the desired changes to flow or pressure at a given pointrelative to the device. The device may be held in its preferred positionand orientation by mechanical struts or inflatable balloons or othersupport mechanisms. These struts or balloons or other support mechanismsmay be located in any number of positions along the device. The strutsor balloons or other support mechanisms may also serve to direct,restrict, block, occlude, or otherwise modify the flow and pressure (andthe enhancements to circulation or perfusion) created by the device.FIG. 34 shows examples of an embodiment of the device located in thebody to provide enhanced circulation or perfusion to specific areas ofthe body. FIG. 34a shows the device placed upstream of the renalarteries with an outlet flow director and nozzle designed to changepressure and flow in the renal arteries. FIG. 34b shows the deviceplaced at the bifurcation of the aorta into the common iliac arteries toenhance circulation to the legs without increasing flow or pressure tothe end-organs. FIG. 34c shows a smaller embodiment of the pump locatedin one renal artery to selectively enhance circulation or perfusion toone kidney only without significantly affecting circulation or perfusionin other areas of the body. In this case, the pump may take up theentire diameter of the vessel, eliminating bypass flow, but stillfunctions effectively. FIG. 34d shows an embodiment of the devicelocated in the inferior vena cava to enhance circulation by increasingvenous return. In general, an embodiment of the present invention may belocated anywhere in the vasculature its size allows. In embodiments inwhich the device comprises one or more flexible cannulas, the positionand orientation of each rigid section can be independently adjusted asdescribed in connection with FIG. 13. For example, FIG. 35 shows a twopump embodiment where one pump sits in the aorta above the renalarteries and the other sits in the aorta below the renal arteries. Ifthe pumps in this embodiment both pump toward the renal arteries, thepressure and flow between the pumps (that is, affecting the renalarteries) may be strongly increased whereas the pressures and flows inregions not between the pumps may be far less strongly increased. Suchfocused augmentation may be useful in cases of sepsis or relatedconditions to increase pressure or flow in the renal arteries withoutstressing or increasing flow through peripheral vessels that may havebeen made leaky by the septic condition.

Step 3d: Position verification made by standard cath-lab techniques asfamiliar to those of ordinary skill in the art.

Step 4: Operate the device for the desired duration and in a mannerintended to provide the targeted or desired pressure or flowaugmentation with for the condition being treated. The pump is switchedon. The pump portion of some embodiments of the current invention maycomprise an electrical motor, the speed of which can be varied from 0%to 100% of full speed and the rotation direction of which can bereversed. In a subset of these embodiments, the speed of the motor canbe varied over this range (e.g. from off to full speed or from fullspeed in one direction to full speed in the other direction) more than150 times per minute. This controllability and variability of the motorspeed may be used to further adjust, modify, control, or augment thepressure and flow changes the device creates. In certain embodiments,the speed or direction of rotation of the electric motor may besynchronized with the native pulse or native pressure or native flow inthe vessel the device is located in. Such synchronization may allowdifferential augmentation of systolic or diastolic pressure and flow. Inother embodiments, the speed or direction of the motor may be preset tochange and vary over time without regard to native pulse or native flowor native pressure. This preset change in speed or direction may occuron an arbitrary timescale. Alternatively, the changes in speed ordirection of the electric motor of the pump device may be synchronizedto some signal from a sensor of body status or function, to some signalfrom an internal or external control unit, or to input from the patientor his doctor. The pumping system of the present invention may beintended for short-term use to increase circulation or perfusion in someorgan or region of the body on an acute basis. The pumping system of thepresent invention may be intended for long-term use to increasecirculation or perfusion in some organ or region of the body on achronic basis.

Step 5: Remove the device. Many embodiments of the present invention maybe removed or relocated by catheter if treatment is complete or if thedevice is not working properly or to move or relocate or adjust ormodify the circulation or perfusion enhancement created by the device.The pump 110 and support structure 120, including support members 121,could be designed whereby pump 110 and support structure 120 could beremoved with a catheter based removal device (not shown) which couldcollapse support members 121 and disengage them from their anchoredconfiguration to permit the removal of them and pump 110, if desired,such as to replace or repair pump 110. Such a catheter based removaldevice could be similar to those presently used with inferior vena cavafilters.

Experimental Example (FIG. 38). The following examples are included todemonstrate particular aspects of the present disclosure. It should beappreciated by those of ordinary skill in the art that the methodsdescribed in the examples that follow merely represent illustrativeembodiments of the disclosure. Those of ordinary skill in the artshould, in light of the present disclosure, appreciate that many changescan be made in the specific embodiments described and still obtain alike or similar result without departing from the spirit and scope ofthe present disclosure.

Experimental and Supporting Data.

Early in vitro studies showed that our device in a low resistance flowloop was capable of generating a 13 mmHg pressure gradient and producingup to 8.5 L/min of flow. Ongoing benchtop studies and computationalfluid modeling have allowed us to reduce the size of our pump whileoptimizing flow and pressure gradients.

To determine the system's acute hemodynamic effects, we deployed thepumps into seven large animals using an esmolol cardiogenic shock model.The results of these studies showed significant increases in cardiacoutput, stroke volume, and ejection fraction.

Beyond the benefits of unloading the heart, we also found that theintravascular pumping module increased pressure to the renal artery by28% and increased renal blood flow by 25% compared to controls (FIG.36). Treatment guidelines to prevent MOF strongly emphasize theimportance of maintaining pressure and flow to the end organs and webelieve our device is uniquely suited to perform this task.

Supporting Data:

The hypothesis that increased pressure and flow in the aorta willbenefit end organ function is supported by previous research done at theTexas Heart Institute using surgically implanted Left Ventricular AssistDevices (LVADs) in a hemorrhagic shock model. This research,investigated the novel use of an LVAD in combination with conventionalfluid and blood resuscitation therapy. They found that LVAD supportafter prolonged hemorrhagic shock led to significant improvements insurvival, markers of end-organ function, and markers of inflammation andanaerobic metabolism (FIG. 37). In addition to markers of organfunction, byproducts of anaerobic metabolism as well as levels ofinflammatory markers have been shown to correlate with clinical severityand prognosis.

Implementations described herein are included to demonstrate particularaspects of the present disclosure. It should be appreciated by those ofskill in the art that the implementations described herein merelyrepresent exemplary implementation of the disclosure. Those of ordinaryskill in the art should, in light of the present disclosure, appreciatethat many changes can be made in the specific implementations describedand still obtain a like or similar result without departing from thespirit and scope of the present disclosure. From the foregoingdescription, one of ordinary skill in the art can easily ascertain theessential characteristics of this disclosure, and without departing fromthe spirit and scope thereof, can make various changes and modificationsto adapt the disclosure to various usages and conditions. Theimplementations described hereinabove are meant to be illustrative onlyand should not be taken as limiting of the scope of the disclosure.

What is claimed is:
 1. A method for adjusting fluid flow or pressurewithin a human body, the method comprising: transluminally inserting apumping system for percutaneous delivery in a desired chamber or adesired vessel of the human body, wherein the pumping system comprises afirst pump implantable in a chamber or vessel of the human body, asecuring means extending from said first pump, wherein said securingmeans secures the first pump in a desired location of said chamber orvessel, and the securing means allows substantially unobstructed flow ofblood around the first pump, one or more inlet ports disposed on saidfirst pump, wherein said inlet ports direct inlet blood flow through thefirst pump, and bypass flow is directed around a pump housing, and oneor more outlet ports disposed on said first pump, wherein said outletports direct at least one high-velocity jet of output blood flow fromthe first pump, and the output blood flow autoentrains the bypass flowto form downstream blood flow, wherein the one or more outlet portscomprise an inducement nozzle that draws the bypass flow into the centerof a lumen, and the at least one high-velocity jet consists of aplurality of jets positioned around the center of the lumen; deployingsaid securing means to secure said pumping system in a lumen of saiddesired chamber or said desired vessel, wherein the pumping system isdeployed in a descending thoracic aorta superior to the celiac, renal,and mesenteric arteries, and the pumping system produces a pressure dropin an aortic root, reduces cardiac afterload, and increases cardiacoutput; and operating the pumping system to cause the at least onehigh-velocity jet of the output blood flow to autoentrain the bypassblood flow.
 2. The method of claim 1, further comprising deploying saidoutlet ports to direct flow to a desire organ or a desired region. 3.The method of claim 1, wherein the outlet ports are oriented to increasepressure or flow to at least one renal artery.
 4. The method of claim 3,further comprising a second pump positioned to pump in a directionopposite a pumping direction of the first pump.
 5. The method of claim4, wherein a first outlet of the first pump and a second outlet of thesecond pump face towards each other.
 6. The method of claim 3, whereinthe one or more outlet ports of the first pump comprise a first outletport directing a portion of the output blood flow to a first renalartery, and a second outlet port directing another portion of the outputblood flow to a second renal artery.
 7. The method of claim 1, whereinthe outlet ports are positioned to increase or decrease pressure in adesired region.
 8. The method of claim 1, wherein the pumping system isdeployed above aortic bifurcation.
 9. The method of claim 1, wherein thepumping system is oriented to adjust flow or pressure to one or morebranching vessels.
 10. The method of claim 1, wherein the pumping systemincreases pressure in the abdominal aorta.
 11. The method of claim 1,wherein the pumping system minimizes reverse bypass flow.
 12. The methodof claim 1, wherein the pumping system increases both pressure and flowdownstream to key end organs.
 13. The method of claim 1, wherein thepumping system maintains pulsatility.
 14. The method of claim 1, whereinthe pumping system enhances kidney perfusion.
 15. The method of claim 1,wherein the first pump is deployed in the descending thoracic aorta neara diaphragm for downward flow, and the one or more outlet ports areconfigured to produce swirl.
 16. The method of claim 1, wherein thefirst pump is deployed just above an aortic bifurcation to produceupward flow that is opposite native flow.
 17. The method of claim 1,further comprising removing the first pump and the securing means whentherapy is complete.
 18. A method for adjusting fluid flow or pressurewithin a human body, the method comprising: transluminally inserting apumping system for percutaneous delivery in a desired chamber or adesired vessel of the human body, wherein the pumping system comprises afirst pump implantable in a chamber or vessel of the human body, asecuring means extending from said first pump, wherein said securingmeans secures the first pump in a desired location of said chamber orvessel, and the securing means allows substantially unobstructed flow ofblood around the first pump, one or more inlet ports disposed on saidfirst pump, wherein said inlet ports direct inlet blood flow through thefirst pump, and bypass flow is directed around a pump housing, and oneor more outlet ports disposed on said first pump, wherein said outletports direct at least one high-velocity jet of output blood flow fromthe first pump, and the output blood flow autoentrains the bypass bloodflow to form downstream blood flow; deploying said securing means tosecure said pumping system in a lumen of said desired chamber or saiddesired vessel, wherein the pumping system is deployed in a descendingthoracic aorta superior to the celiac, renal, and mesenteric arteries,and the pumping system produces a pressure drop in an aortic root,reduces cardiac afterload, and increases cardiac output, wherein furtherthe outlet ports are oriented to increase pressure or flow to at leastone renal artery, and the one or more outlet ports of the first pumpcomprise a first outlet port directing a portion of the output bloodflow to a first renal artery, and a second outlet port directing anotherportion of the output blood flow to a second renal artery; and operatingthe pumping system to cause the at least one high-velocity jet of theoutput blood flow to autoentrain the bypass blood flow.
 19. The methodof claim 18, wherein the pumping system maintains pulsatility.